EP1425063B1 - Systeme permettant de detecter une fuite dans un conduit de fluide - Google Patents

Systeme permettant de detecter une fuite dans un conduit de fluide Download PDF

Info

Publication number
EP1425063B1
EP1425063B1 EP02761044A EP02761044A EP1425063B1 EP 1425063 B1 EP1425063 B1 EP 1425063B1 EP 02761044 A EP02761044 A EP 02761044A EP 02761044 A EP02761044 A EP 02761044A EP 1425063 B1 EP1425063 B1 EP 1425063B1
Authority
EP
European Patent Office
Prior art keywords
blood
air
fluid
negative pressure
circuit
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Expired - Lifetime
Application number
EP02761044A
Other languages
German (de)
English (en)
Other versions
EP1425063A2 (fr
EP1425063B2 (fr
EP1425063A4 (fr
Inventor
James Brugger
Jeffrey Burbank
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
NxStage Medical Inc
Original Assignee
NxStage Medical Inc
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Family has litigation
First worldwide family litigation filed litigation Critical https://patents.darts-ip.com/?family=25412386&utm_source=google_patent&utm_medium=platform_link&utm_campaign=public_patent_search&patent=EP1425063(B1) "Global patent litigation dataset” by Darts-ip is licensed under a Creative Commons Attribution 4.0 International License.
Application filed by NxStage Medical Inc filed Critical NxStage Medical Inc
Publication of EP1425063A2 publication Critical patent/EP1425063A2/fr
Publication of EP1425063A4 publication Critical patent/EP1425063A4/fr
Publication of EP1425063B1 publication Critical patent/EP1425063B1/fr
Application granted granted Critical
Publication of EP1425063B2 publication Critical patent/EP1425063B2/fr
Anticipated expiration legal-status Critical
Expired - Lifetime legal-status Critical Current

Links

Images

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/36—Other treatment of blood in a by-pass of the natural circulatory system, e.g. temperature adaptation, irradiation ; Extra-corporeal blood circuits
    • A61M1/3621—Extra-corporeal blood circuits
    • A61M1/3626—Gas bubble detectors
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/36—Other treatment of blood in a by-pass of the natural circulatory system, e.g. temperature adaptation, irradiation ; Extra-corporeal blood circuits
    • A61M1/3621—Extra-corporeal blood circuits
    • A61M1/3653—Interfaces between patient blood circulation and extra-corporal blood circuit
    • A61M1/3656—Monitoring patency or flow at connection sites; Detecting disconnections
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/13—General characteristics of the apparatus with means for the detection of operative contact with patient, e.g. lip sensor

Definitions

  • the invention relates to a fluid infusion or treatment system according to the preamble of claim 1.
  • the present invention generally relates to the detection of leaks (including needle-disconnects and other causes of loss of integrity) in extracorporeal blood circuits and more particularly to the application of air infiltration detection techniques to the detection of leaks in positive pressure return lines.
  • US-A-5 120 303 discloses a dialysis apparatus comprising a reversible pump to remove blood from patient for treatment thereof and for returning purified blood to the patient.
  • One technique for extracorporeal blood processing employs a single "access,” for example a single needle in the vein of the patient or a fistula.
  • a volume of blood is cyclically drawn through the access at one time, processed, and then returned through the same access at another time.
  • Single access systems are uncommon because they limit the rate of processing to half the capacity permitted by the access.
  • two-access systems in which blood is drawn from a first access, called an arterial access, and returned through a second access, called a venous access, are much faster and more common.
  • These accesses include catheters, catheters with subcutaneous ports, fistulas, and grafts.
  • extraction of a needle disconnection of a luer
  • poor manufacture of components cuts in tubing, and leaks in a catheter.
  • the most reliable solution to this risk that of direct and constant trained supervision in a safe environment, has an enormous negative impact on the lifestyles of patients who require frequent treatment and on labor requirements of the institutions performing such therapies.
  • ultra-safe systems that can be used in a non-clinical setting and/or without the need for highly trained and expensive staff.
  • One of the risks for such systems is the danger of leaks.
  • a number of companies have dedicated resources to the solution of the problem of leak detection.
  • loss of blood through the patient access and blood circuit can be indirectly detected by detecting the infiltration of air during the draw cycle.
  • Air is typically detected using an ultrasonic air detector on the tubing line, which detects air bubbles in the blood. The detection of air bubbles triggers the system to halt the pump and clamp the line to prevent air bubbles from being injected into the patient. Examples of such systems are described in US Patent Nos. 3,985,134 , 4,614,590 , and 5,120,303 .
  • the first level of protection against return line blood loss is the use of locking luers on all connections, as described in International Standard ISO 594-2 which help to minimize the possibility of spontaneous disconnection during treatment. Care in the connection and taping of lines to the patient's bodies is also a known strategy for minimizing this risk.
  • a higher level of protection is the provision of venous pressure monitoring, which detects a precipitous decrease in the venous line pressure.
  • This technique is outlined in International Standard IEC 60601-2-16. This approach, although providing some additional protection, is not very robust, because most of the pressure loss in the venous line is in the needle used to access the patient. There is very little pressure change in the venous return line that can be detected in the event of a disconnection, so long as the needle remains attached to the return line. Thus, the pressure signal is very weak. The signal is no stronger for small leaks in the return line, where the pressure changes are too small to be detected with any reliability.
  • One way to compensate for the low pressure signal is to make the system more sensitive, as described in US Patent No.
  • US Patent No. 6,177,049 B1 suggests the idea of reversing the direction of blood flow for purposes of patency testing and access-clearing.
  • the patency tests alluded to by the '049 patent refer simply to the conventional idea of forcing blood through each access to clear occlusions and to ascertain the flow inside a fistula.
  • the invention provides a system according to claim 1. Further embodiments of the invention are described in the dependent claims.
  • Leaks in the arterial portion of a two-access extracorporeal blood circuit can be very reliably detected because the arterial access line is generally under negative pressure.
  • any loss of integrity of the arterial circuit - at least those parts under negative pressure - will result in the infiltration of air into the circuit, which can then be detected by an ultrasonic air bubble detector.
  • the air bubble detector is so reliable that, since its introduction in the 1970's no deaths have been attributed to the failure of this technology to detect a leak.
  • the same technique can be applied to the physical parts of the circuit that are ordinarily under positive pressure by intermittently subjecting them to negative pressure throughout treatment.
  • the venous side of the circuit is subjected to a negative pressure thereby causing air to infiltrate, through any openings in the circuit such as caused by a leak, a loose needle, or a disconnected luer.
  • a conventional air detector such as an ultrasonic detector, may then be relied upon to detect the loss of integrity and an appropriate response generated.
  • Other technologies, such as radio frequency detection technology, direct audio detection of infiltration using a hydrophone, and others may also be used.
  • the flow of blood from the arterial access to the venous access is periodically reversed.
  • This causes a negative pressure in the venous part of the circuit which, if compromised by a loose or extracted needle or leak, will result in detectable air infiltration.
  • the air infiltration may be detected by the same means used for detecting leaks in the arterial part of the circuit.
  • the flow reversal technique can allow the same leak detection device to be used for detecting both venous circuit leaks and arterial circuit leaks, as long as the flow of blood is controlled in such a way as to insure that any resulting bubbles arrive at the air detector.
  • the period of the flow reversal cycles may be made no greater than a ratio of the maximum allowable blood volume loss to the volume flow rate of the blood. Note that in determining this quantity, due consideration should be given to the fact that some of the patient's blood is already outside of his/her body in the circuit of the machine. Thus, if the maximum blood loss a patient can tolerate is 500 ml. and the rate of flow of blood is 500 ml./min., the period of the flow reversal cycles may be made no greater than one minute to insure a high level of security.
  • One technique for reversing the flow in a two-access circuit is to reverse the pump.
  • Another technique is to provide separate pumps, one for each flow direction. At each moment only one pump would run, while the idle pump would either block flow if plumbed as a parallel circuit, or permit flow (e.g., a bypass), if plumbed as a series circuit.
  • Another technique for providing flow reversal is to employ a four-way valve, which is a four-port valve that transposes the interconnections between the inputs and outputs of the pump and those of the venous and arterial circuits, respectively.
  • four-way valves that may be used to accomplish this are described in US Patent Nos. 5,894,011 , 5,605,630, 6,177,049 , 4,885,087 , 5,830,365 , and 6,189,388 .
  • These prior art valves either suffer from being non-hermetic so that they have seals; are intended to be reused; have stagnant zones, or are simply too expensive.
  • a preferred configuration of a four-way valve defines an H-shaped bridge that is alternately pinched by respective perpendicular anvil-edges to form alternate flow configurations.
  • a first anvil-edge pinches the H-shaped bridge at the center of the crossing line of the "H" to form mirror image U-shaped channels.
  • a second anvil edge perpendicular to the first, pinches the bridge to bisect it and form two parallel channels.
  • Various other hermetic configurations are possible, preferably each provides a four-way valve function and no dead (i.e., no-flow) spaces, which could cause clotting or other deleterious effects, within the valve.
  • negative pressure in the venous line is generated in just the return circuit. This may be done by periodic paroxysmal expansion of a bladder plumbed inline in the venous circuit. The sudden expansion generates a negative pressure in the venous circuit, drawing air into the blood and exposing any loss of integrity via an appropriately-located air infiltration detector.
  • a source of fluid 120 supplies fluid to a drive/negative pressure device 100 that does at least two things: it moves the fluid to the patient and it selectively generates negative pressure. It may also incorporate, or be connected with, a treatment process 130, for example a hemofiltration, hemodialysis, hemodiafiltration, or other blood treatment process.
  • a fluid circuit connects the drive/negative pressure device 100 to an air sensor 105, which is in turn connected to a tested fluid circuit 110 whose leak-integrity must be assured. Finally, fluid is introduced into a patient 115. Note that in some embodiments, the drive/negative pressure device 100 may be transposed with the air sensor 105, as long as it is assured that any leaks in the tested circuit 110 will arrive at at least one air sensor. Air sensors may be arranged in the tested circuit as well.
  • the source of fluid 120 is most likely blood from the patient 115, as would be the case for an extracorporeal blood treatment process such as hemofiltration or dialysis. That is, the circuit 120, 100, 105, 110, may be a two-access draw/return circuit with some sort of treatment process 130 connected with it. However, the source of fluid could also be a storage vessel in a single access circuit or a quantity of blood being transfused or infused.
  • the essential feature of the circuit of Fig. 1 is that it is a supply circuit generally introducing fluid to the patient 115.
  • the air sensor 105 detects air bubbles in the tested circuit when the flow of fluid is reversed in at least a portion of the tested circuit 110 by the inducement of negative pressure in the tested circuit 110 by the drive/negative pressure device 100.
  • the tested circuit 110 may include any part of an extracorporeal treatment circuit where there is ordinarily a positive pressure applied to the fluid (blood, in that case) such that a leak in the tested circuit 110 would result in a loss of blood.
  • the drive/negative pressure device 100 generates a negative pressure on some intermittent schedule such that, at most times, fluid flows from the source 120 to the patient 115.
  • the negative pressure is temporarily generated in the tested circuit 110.
  • the negative pressure will draw air through any leaks in the tested circuit 110, which will appear as detectable air bubbles, triggering the air sensor 105.
  • one possible embodiment of the drive/negative pressure device 100 is simply a reversible pump 200.
  • the pump 200 could be, for example, a peristaltic pump whose direction of rotation can be reversed. It could be any type of pump that can be reconfigured, such as by rotating a drive in a reverse direction, to reverse flow.
  • the flow-reversal effect of this embodiment produces a negative pressure in the tested circuit 110 thereby drawing air into it and permitting detection of loss of integrity by the air sensor 105.
  • FIG. 3 another possible embodiment of the drive/negative pressure device 100 is a pair of pumps 230, 235 and 240, 245.
  • a parallel configuration 232 only one pump 230, 235 is actuated at a time, while the other 230, 235 blocks flow while it is idle to prevent short-circuiting.
  • a series configuration 242 only one pump 240, 245 is active at a time while the idle pump 240, 245 permits blood to flow through it.
  • the flow reversal caused by both embodiments has the same effect as the embodiment of Fig. 2 .
  • FIG. 5 still another possible embodiment of the drive/negative pressure device 100 employs a single pump 255 that pumps in a single direction.
  • a four-way valve 260 transposes the input 256 and output 257 between the source of fluid 120 and the patient 115 such that a flow reversal results, as in the embodiments of Figs. 2-4 .
  • a treatment process 130 is arranged in series with the pump 255.
  • a single pump 270 that pumps in a single direction. Downstream of the pump 270, a bladder 280 forms part of the continuous exiting blood circuit.
  • the bladder 280 may be expanded by a vacuum applied to a rigid casing 275, for example by a suction device such as a vacuum pump 285.
  • the vacuum pump 285 may incorporate ballast because of the less-than-unity duty cycle of the negative pressure inducement cycle. Rapid expansion of the bladder 280 causes a negative pressure in the tested circuit with an effect that is generally similar to that of the foregoing embodiments.
  • the pump 270 may or may not be deactivated.
  • an alternative device for creating a negative pressure is a syringe 279 with a cylinder 278 and piston 276 driven by an automatic actuator 277. Note that, depending on the configuration of other components of the system to which the bladder 280 or syringe 279 (or equivalent device) is connected, it may be necessary to include a valve (not shown) to prevent backflow.
  • a blood processing machine 700 processes blood supplied to it from a patient 710 via a leak detection device 705.
  • the blood processing machine 700 may be any type of device including hemodialysis, hemofiltration, hemodiafiltration, blood and blood component collection, plasmaphresis, aphresis, and blood oxygenation.
  • the leak detection device 705 is configured such that blood flows as indicated by the arrows 706 and 707.
  • the leak detection device 705 can be added to any type of conventional or as yet unknown type of blood processing machine to provide return side leak detection.
  • FIG. 7B one embodiment of the leak detection device 705 is shown at 720.
  • the latter includes a circuit with a four-way valve 722 and an air sensor 724.
  • a circuit is formed joining draw 707 and return 708 lines from the patient with the corresponding lines 702 and 703 of the blood processing machine through the four-way valve 722.
  • the four-way valve 722 reverses the blood flow on the patient-side of the circuit without affecting the direction of blood flow through the blood processing machine 700.
  • An air sensor 724 detects air in either the draw line 707 during forward operation and in the return line 708 during reverse operation.
  • an alarm may be actuated or the circuit may be clamped to halt blood flow, thereby triggering a malfunction response in the blood processing machine 700 as illustrated in detail in the particular embodiment of Fig. 7E .
  • the air sensor 724 is not essential for practicing the invention if an air sensor is located in the blood processing machine 700. In that case, control of the leak detection device 720 would have to insure that enough fluid is displaced to permit detection by the air sensor in the blood processing machine 700.
  • a leak detection device 730 which can be added to an infusion pump 725, includes an automatic syringe or reverse pump 735 and an air sensor 740.
  • a controller (not shown) causes the syringe or reverse pump 735 to reverse the flow through a circuit 737 leading to the patient 710 automatically.
  • the air sensor 740 detects any air drawn into the circuit 737 caused by any leaks.
  • the same air sensor 740 can detect any leaks upstream of it at times when the syringe, or reverse pump 735, is not actuated.
  • the syringe or reverse pump 735 may be replaced by any suitable device such as that of Figs. 6A or 6B , a diaphragm pump, or any other suitable mechanism for creating a negative flow in a tested circuit.
  • an infusion pump 744 draws fluid from a reservoir 743 via a pump 742.
  • An air sensor 746 detects any bubbles in the fluid stream.
  • a controller 741 periodically reverses direction drawing air into the circuit 747, which can be detected during the reverse operation and responded to by an alarm, shutdown, or other appropriate action.
  • a blood processing machine 745 and leak detection device 750 are interconnected as discussed with reference to Fig. 7A .
  • the blood processing machine 745 contains a pump 775 and a filter or dialyzer 780.
  • the leak detection device contains a four-way valve 782, which transposably interconnects the draw and return lines 751 of the blood processing machine 745 and the draw and return lines 752 of the patient 710 access.
  • a controller 778 periodically and automatically switches the four-way valve 782, thereby causing air to enter any leaks in a return line and to be detected by an air sensor 776.
  • the controller monitors the air sensor and may respond by actuating a clamp 777 and/or triggering an alarm 779. Actuating the clamp 777 can be used to trigger a malfunction response by the blood processing machine 745, which may have, for example, a pressure switch that would be activated by a clamped line.
  • Fig. 7F leak detection features are built combined with those of a blood processing machine to form an integrated leak detecting blood processing machine 783.
  • the latter contains air sensors 760 and 770, a filter 780, and a reversible pump 775, the latter being one mechanism for reversing flow to test the return circuit as discussed above in connection with other embodiments.
  • two air sensors 760 and 770 may quickly detect any leaks in draw and return accesses 762 and 763 when the pump is driven in forward and reverse directions, respectively.
  • the 7F also contains an additional leak detection feature by defining a funnel 790 at the bottom of an enclosure housing a housed portion 784 of a blood circuit 764 with a fluid detector 785 at the bottom of the funnel 790. Any leaks occurring in the housed portion 784 will be directed by the funnel 790 toward the fluid detector 785.
  • the fluid detector 785 may be any suitable device for detecting blood, for example, a continuity tester.
  • the fluid detector 785 may be linked to the same alarm system as the air sensors 760 and 770 and be responded to in the same manner as discussed in connection with any of the embodiments described herein.
  • a reservoir 805 of fluid to be infused is pumped through an infusion pump 800.
  • the infusion pump has a pump 830, a four-way valve 810, and one or more air sensors 803.
  • the four-way valve 810 is set to infuse fluid from the reservoir 805 to the patient 840.
  • the four-way valve 810 is controlled to reverse periodically to check for leaks.
  • the four-way valve 810 is connected such that fluid (which may include blood) flows back toward the one or more air sensors 803 indicating a leak.
  • an example of a two-access blood processing system 300 (illustrated as one for performing a hemofiltration or dialysis) combines a conventional blood processing machine (shown as a hemofiltration or dialysis machine) 301 with a venous disconnect sensor device 303.
  • the blood processing machine 301 may be of standard design with a separate venous disconnect sensor device 303 connected to it to provide the functionality of the embodiment of Fig. 1 .
  • the separate venous disconnect device 303 allows retrofit of conventional blood processing machine 301 to provide the safety benefits of the invention.
  • the blood processing machine 301 contains a dialyzer or hemofilter 305, which filters the blood passing through it.
  • the dialyzer or hemofilter 305 contains connections 355 and 356 to a waste fluid or dialysate circuit and arterial 361 and venous 362 connections of a treatment circuit 302.
  • a pump 310 which is illustrated by a peristaltic pump, pumps blood through the dialyzer or hemofilter 305, draws blood from the patient 335, and returns blood to the patient 335. Blood passes through the dialyzer or hemofilter 305 in one direction through a four-way valve 315 and then into a venous access 341 into the patient 335. Blood is drawn from an arterial access 340, passes through the four-way valve 315, and is supplied to the pump 310.
  • the blood processing machine 301 includes a venous return air sensor 320 located near the outlet of the dialyzer or hemofilter 305 in the treatment circuit 302. The latter detects any air in the blood prior to the blood being returned to the patient.
  • the venous return air sensor 320 is standard on blood processing machines such as the hemofiltration and dialysis machine 301 and may be any type of air detector. For example, it may be an ultrasonic bubble detector as commonly used for detecting leaks in blood processing equipment.
  • a venous line clamp 325 selectively cuts off flow downstream of the venous return air sensor 320 as standard on blood processing equipment.
  • the draw line air sensor 345 detects air in the arterial line downstream of the four-way valve 315 and upstream of the pump 310.
  • Fig. 8B periodically, the four-way valve 315 is switched to a reverse-flow position to cause blood to be drawn through venous access 341 and returned through the arterial access 340.
  • the configuration of Figs. 8A and 8B is instated only temporarily to cause air to infiltrate the venous circuit 342 through any leaks or disconnections in the venous circuit 342. The air infiltration may then be detected by the air sensor 345.
  • the disclosed embodiment need not have the air sensor 345, but could rely for testing the venous circuit 342 on the air sensor 320 if the blood processing machine 301 has one. The only requirement would be that the flow be reversed long enough to displace any air bubbles from the leak to a point beyond the four-way valve 315 so that the pump will convey the air bubbles to the air sensor 320.
  • the line clamp 322 is actuated shutting down flow through it and triggering a safety shutdown in the blood processing machine 301.
  • a safety mechanism that when flow through the blood processing machine 301 is halted, because of a fault like a crushed line for example, a venous pressure monitor 350 is triggered due to a resulting rise in venous pressure. This causes the blood processing machine 301 to stop the pump 310, set off an alarm, and clamp venous line clamp 325.
  • the venous disconnect sensor device 303 is provided with an alarm 330, such as an audio and/or visual signal to alert an operator to the shutdown.
  • the venous disconnect sensor device 303 may be connected to and used with a variety of different blood processing machines. Alternatively, its functionality may be integrated in any such machine. Also note that although the alarm event was described in the above embodiments as being triggered by a venous pressure monitor in the blood processing machine 301, it could be configured such that the air sensor 345 triggers an alarm directly.
  • the entire tested blood circuit 110 of Fig. 1 and an entire blood circuit 311 ( Fig. 8A ) of the two-access hemofiltration system 300 may form a disposable unit.
  • Another desirable attribute of the components of a blood circuit is that it be hydraulically continuous, that is, that it provide no dead spaces that could cause stagnation of some of the blood flow.
  • Another sometimes-beneficial feature of the components is that they be free from surfaces that rub together or have potentially stagnant capillary spaces such as seals. Together, these cost and hydraulic continuity requirements can impose significant constraints on the design of the four-way valve 315.
  • a complete blood processing system with leak detection 1001 may conform to the details of the embodiment of Figs. 8A and 8B .
  • the line clamp 322 of Figs. 8A and 8B may be omitted.
  • the air sensor 345 may be omitted, if desired, although it may provide an advantage of making it possible to detect leaks earlier.
  • Components of Fig. 8C perform essentially the same functions as the identically-labeled components of Figs. 8A and 8B and are therefore not discussed further.
  • a four-way valve body 405 is formed of a compliant injection moldable polymer.
  • the valve body 405 has four ports 411, 412, 413, and 414.
  • Each port has a flanged portion, for example as indicated at 410, permitting tubing to be inserted and bonded to the valve body 405.
  • Each port 411, 412, 413, and 414 may be selectively joined to either of two adjacent ports by forcing an anvil-edge 415 against the center of the valve body 405 in one of two orthogonal directions as shown in Figs. 9B and 9C .
  • the anvil-edge is pressed in a first direction joining ports 411 and 412 and simultaneously joining ports 413 and 414.
  • the anvil-edge is pressed in a second direction joining ports 411 and 414 and simultaneously joining ports 412 and 413.
  • the flow passages form by pinching the valve body 405 are free of dead flow zones in both configurations.
  • a valve body 430 is formed in the shape of an "H."
  • an anvil-edge is perpendicular to the first orientation and pinches the bridge to bisect it and form two parallel channels 460.
  • the anvil-edge 450 pinches the H-shaped bridge 455 longitudinally along the centerline of the crossing line 455 of the "H” to form mirror image U-shaped channels 457.
  • the anvil edges 415, 450 may be actuated by solenoids.
  • solenoids Referring now to Figs. 11A-11D , one way to activate both orientations of the anvil edge 405/415, 450 with a single solenoid is by disposing two perpendicular anvils 510 and 515 on opposite sides of the valve body 540.
  • One anvil 515 may be urged toward the valve body 540 by a spring 550 while the other is forced by the solenoid 560.
  • the solenoid 560 is retracted, only the spring-urged anvil 515 deforms the valve body 540.
  • solenoid-forced anvil 510 deforms the valve body 540.
  • Fig. 11A shows the spring urged anvil 515 is pressed along the bridge (parallel to the length of the bridge of the "H") as viewed from the side and Fig. 11B shows the same configuration as viewed from the top.
  • Fig. 11C shows the solenoid urged anvil 510 pressed across and bisecting the bridge of the "H" as viewed from the side and Fig. 11D shows the same configuration as viewed from the top.
  • Support tables 520 and 525 provide support for parts of the valve body 540 that are not otherwise supported by the anvils 510 and 515.
  • Fig. 1 may be provided in a fully integrated system rather than as an add-on to a conventional blood processing machine 301 as illustrated in the embodiment of Figs. 8A and 8B . That is, the components of the venous disconnect sensor device 304 may be integrated in the blood processing machine 301 as is readily apparent from the figure.
  • the air sensors 320 and 345 may be combined with other sensing mechanisms in a fuzzy logic circuit or network classifier to enhance the robustness and sensitivity of leak detection.
  • the inventive technique may be combined, for example, with fluid sensing as described in PCT application US98/19266 , combined with venous pressure monitoring as outlined in International Standard IEC 60601-2-16.
  • a control mechanism for an embodiment of the invention includes a controller 601, which could be a programmable microprocessor, mechanical, or electromechanical controller.
  • the controller 601 is connected to receive inputs from an air sensor 604 and, optionally, other sensors 607.
  • the controller 601 is also connected to control an alarm output 606, a pump 602, and a four-way valve 603.
  • the controller 601 may control other types of drive/negative pressure devices 100 as should be clear from the present disclosure.
  • the other sensors 607 may include any (or none) of the fluid detectors and pressure sensors or any other sensors including those of the prior art.
  • any, or all, of the sensor inputs may be used in combination or alone to trigger an alarm state, preferably one accompanied by shutdown of the pump 602.
  • the air sensor 604 may be any kind of sensor capable of detecting either the intrusion of air into a circuit or the presence of air in the circuit. Air infiltrating a line may create sound for example, as bubbles 683 are generated by the infiltration. Such a sound may be detected with, for example, an audio sensor such as a hydrophone 684. A signal from a hydrophone 684 could be classified by an audio pattern recognition engine programmed into the controller 601 to screen out other sounds. In such a case, in the embodiments discussed above, air does not need to be drawn all the way to the air sensor 604 for infiltration to be detected; rather the audio signals may travel through the lines 682 in the fluid media to the sensor 684.
  • a hydrophone may be detect sounds without being immersed in the fluid itself, as long as appropriate acoustic measures are taken to minimize attenuation through any barriers.
  • Other types of disturbances or machine-recognizable features may form a basis for detecting air infiltration such as optical, vibrational, chemical, etc.
  • controller 601 need not be the ultimate originator of command signals for the reversing (or negative pressure) cycles. So, for example, a signal for triggering the reversing (negative pressure) cycles could originate from a different source, for example a conventional blood processing system and be converted into a control signal by a final control (e.g. 601) to govern the reversing (negative pressure) cycle. Such an embodiment would be well within the scope of the invention as claimed below.
  • the controller 601 may also be responsible for controlling the timing of the periodic flow reversals.
  • the pump 602 may be configured to output encoder pulses to the controller 601 to allow the controller 601 to cumulate the volume of blood displaced in a given direction.
  • Figs. 8A and 8B in addition to Fig. 12A , in normal operation, the system of Figs. 8A and 8B pumps blood from the arterial access 340 processes it, and returns treated blood to the patient through a venous access 341.
  • the peristaltic pump, 310 it is possible by counting the number of rotations of the pump to determine accurately the volume of blood displaced.
  • a maximum tolerable blood loss may be determined and used to control the periodic negative pressure cycles, for example in the hemofiltration system 300. Note that in determining maximum limits, due consideration must be given to the fact that some of the patient's blood is already outside of his/her body in the circuit of the machine.
  • the period of the flow reversal cycles can be set to a value that is no greater than a ratio of the maximum allowable blood volume loss to the volume flow rate of the blood.
  • the period of the flow reversal cycles should be no greater than one minute.
  • the period between cycles can be determined by calibrated timing, by direct measurement of mass or volume flow, or by other means effective to insure the amount of blood does not go beyond some safe limit.
  • each negative pressure cycle is best determined by how long it takes to draw the entire quantity of blood in the circuit between the terminal end of the patient's venous access and a point where it is inevitable that the infiltrated air will reach an air detector (e.g., 345). In a system with a four-way valve, this may be the point where the air is just beyond the four-way valve, where the blood runs through the circuit in the same direction irrespective of the position of the four-way valve. For example, in the embodiment of Figs.
  • the pump will insure that it gets to the air sensor 345 once it is on the treatment circuit 302 side of the four-way valve 315, which only runs in direction.
  • the duration of the, negative pressure cycle need only insure that a leak at the most remote end would cause air bubbles to be drawn all the way to an air sensor.
  • control protocols although not required, are desirable. These protocols may be implemented by suitably calibrated timing of control signals, by counting pump revolutions, by direct measurement of blood flow volume, or any other suitable technique.
  • the maximum allowable blood loss which may be used to determine the maximum time between leak test cycles, may be made a programmable value that can be entered in the controller 601. Each patient may be evaluated and a maximum threshold established specifically for him/her. Alternatively, the controller could be connected to an electronic scale, which generates a maximum tolerable blood loss value based on the patient's weight.
  • a peristaltic pump was disclosed, this is only an example and it is clear that a variety of different types of pumps may be used with the invention.
  • a diaphragm or turbine pump may also be used in place of any of the pumps disclosed.
  • a four-way valve, a reversible pump, an expanding bladder, and connected pairs of pumps were described as mechanisms for reversing flow, it is clear that other mechanisms can also be employed.
  • Each of the examples of a pump and a valve or reversible pump, or pump combinations amounts to a different reversible conveyance. Note also that it is possible to practice the invention, as indicated in the discussion of Figs.
  • hemofiltration or dialysis application of the invention was described, it is clear the invention is applicable to many different systems in which blood is circulated outside the body.
  • the system may be used to avoid waste of blood or insure the satisfaction of a critical need, during transfusion.
  • Some other examples of applications are hemodialysis, hemofiltration, hemodiafiltration, blood and blood component collection, plasmaphresis, aphresis, and blood oxygenation.
  • a fluid other than blood may be drawn or injected for line-testing purposes rather than relying solely on blood drawn from the return line. This may be useful in instances where the venous access cannot supply a great deal of blood.
  • sterile fluid from a reservoir 601 may be allowed to flow into a junction 605 through a cutoff valve 610 when the flow is reversed or a negative pressure generated. Any leaks would be detectable in the fluid, as they are detected, as discussed above.
  • the only blood that need be drawn through a draw access 615 is the volume necessary to fill the circuit 620 between the remote terminus 625 of the access and the junction 605.
  • a control system 630 may open the cutoff valve 610 permitting fluid from the reservoir 601 to enter the junction 605 only after at least a sufficient volume of blood had been drawn from the remote terminus 625 to fill the circuit between the remote terminus 625 and the junction 605.
  • a volume of fluid, possibly along with blood, would then be drawn at least sufficient to fill the circuit between the point where it is inevitable that the air will arrive at an air sensor 640.
  • the volume might be the volume of the circuit from the remote terminus 625 right up to (or sufficiently near) the air sensor 640 to be detected.
  • the fluid may be drained to a waste collection container 635 or returned to the patient.
  • the former option may be implemented through a suitable flow diverter mechanism 637 such as used to let fluid in.
  • a single air sensor is shown. It is clear that multiple air sensors may be used in a single line and spaced apart by an equal volume of displaced fluid/blood so that the volume of blood/fluid that must be pumped in reverse can be reduced. Thus, referring to Fig. 14 , if a two air sensors 650 are used in a given circuit portion 655 rather than only one, the amount of fluid/blood that has to be displaced in the circuit in order to test it fully for leaks can be reduced substantially by half.
  • a blood line 655 has two access ends 660 and 665 adapted to be connected to a patient for draw and return of blood.
  • Two filter ends 670 and 675 are connected by a valve portion 680 to the access ends 660 and 665 and adapted to be connected to a filter or other treatment device (not shown).
  • the filter ends 670 and 675 may be connected to a filter (not shown) at the point of manufacture and sealed and sterilized with the entire blood line shown.
  • the valve portion 680 preferably, is a blood contact portion of a complete flow diverting device that may be, for example, the valve body parts 405, 430, 540 of the four-way valves illustrated in Figs.
  • the valve portion 680 switches the direction of the flow of blood between the access ends 660 and 665.
  • the bloodline 655 also has a portion 656 adapted to be driven by a pump, such as a peristaltic pump (not shown).
  • the bloodline of Fig 15 may be a replaceable device that is packaged with instructions 667 explaining how it may be used with a blood processing machine such as any of the embodiment discussed above. It may be configured to provide the fluid conveyance line for both the blood processing machine and leak detection device portions of any of the above embodiments, such as embodiments configured along the lines of Fig. 7A or complete systems like.
  • the blood line 655 has only the basic elements, and in a practical implementation would be expected to include one or more of the following: injection sites, luer connectors, drip chambers, transducer protectors, manual line clamps, access lines, access needles, dialyzers, filters, protective caps, etc.
  • the entire blood line is manufactured and then sterilized, for example, by gamma rays, steam, or other means.
  • inventive leak detection method and device are applied to extracorporeal blood circuits
  • the invention has other applications as well.
  • circuits used for infusion of costly (or time-critical) drugs may be monitored using the invention.
  • Fig. 16 shows a generalized liquid conveyance system in which a liquid is conveyed from a source 905 to a sink 910.
  • a pump 925 forces the liquid along a channel 915 whose integrity is to be tested.
  • An air sensor 920 is located at some point along the line.
  • a throttling device 930 may or may not be required.
  • the liquid is conveyed from source 905 to sink 910 under positive pressure in the channel 915. Automatically and repeatedly, a negative pressure is generated in the channel 915, for example by operating the pump 925 in reverse.
  • the negative pressure draws air into the liquid in the line if there are any leaks in the line.
  • the air is detected by the air detector 920 and the leak is revealed.
  • Any liquid conveyance system may be tested in this way, as long as a negative pressure can be generated selectively using any of the techniques (or any others) as discussed above.
  • the source and sink may be identical.
  • the system might circulate liquid through a processing system such as a heat exchanger or a reaction processor with a catalyst or other such processing system.
  • leaks are betrayed by the detection of a presence of air into the tested line
  • other techniques are possible in other embodiments of the invention. For example, rather than detect a presence of air, it is possible to detect the infiltration of the air as it occurs.
  • an acoustic signal may be generated by bubbles as they are drawn into the tested circuit. This signal may be detected by an acoustic sensor.
  • air bubbles flowing through the line may be detected by other means such as an acoustic signal of bubbles passing by an acoustic sensor.
  • Various velocimetry techniques are affected by air, for example vortex shedding velocimeter, orifice plates, and other such devices.
  • the presence of air may be detected by optical means as well.

Landscapes

  • Health & Medical Sciences (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Vascular Medicine (AREA)
  • Biomedical Technology (AREA)
  • Engineering & Computer Science (AREA)
  • Anesthesiology (AREA)
  • Cardiology (AREA)
  • Hematology (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • External Artificial Organs (AREA)
  • Examining Or Testing Airtightness (AREA)

Claims (4)

  1. Système d'infusion ou de traitement de fluide comprenant :
    une source de fluide (120),
    un dispositif de pression négative / d'entraînement (100, 602) qui est raccordé à la source de fluide (120) et grâce auquel le fluide peut être déplacé de la source de fluide (120) jusqu'à un patient (115) via un circuit de fluide éprouvé (110), et
    un contrôleur (601) raccordé au dispositif de pression négative / d'entraînement (602) et adapté pour contrôler le dispositif de pression négative / d'entraînement (100, 602) pour déplacer le fluide à partir de la source de fluide (120) via le circuit de fluide éprouvé (110) jusqu'au patient (115) en appliquant une pression positive au fluide de sorte qu'une fuite dans le circuit éprouvé (110) se traduirait par une perte de fluide,
    caractérisé par :
    un détecteur d'air (105, 604) raccordé au circuit de fluide éprouvé (110) et au contrôleur (601), dans lequel le contrôleur (601) est adapté pour contrôler le dispositif de pression négative / d'entraînement (100, 602) afin de générer temporairement une pression négative dans le circuit éprouvé (110) à certains intervalles pour aspirer ainsi de l'air à travers toute fuite dans le circuit éprouvé (110), lequel air déclenche le détecteur d'air (105, 604) pour détecter une fuite dans le circuit éprouvé (110).
  2. Système selon la revendication 1, dans lequel le dispositif de pression négative / d'entraînement (100, 602) est une pompe réversible (200) ou comprend une paire de pompes (230, 235 ; 240, 245) avec une pour chaque direction d'écoulement ou comprend une pompe (255) et un robinet à quatre voies (260).
  3. Système selon les revendications 1 ou 2, le système étant prévu dans une machine de traitement de sang, le fluide étant du sang, dans un récipient de stockage.
  4. Procédé selon l'une quelconque des revendications 1 à 3, comprenant en outre une conduite de puisage (762, 341), via laquelle le fluide est déplacé de la source de fluide (120) jusqu'au patient (115) lorsque la pression positive est appliquée par le dispositif de pression négative / d'entraînement et une conduite de retour (763, 340), via laquelle le fluide revient du patient (115) à la source de fluide lorsque la pression négative est appliquée par le dispositif de pression négative / d'entraînement, dans lequel un filtre (F) est agencé dans la conduite d'aspiration (762, 341).
EP02761044.3A 2001-07-07 2002-07-08 Systeme permettant de detecter une fuite dans un conduit de fluide Expired - Lifetime EP1425063B2 (fr)

Applications Claiming Priority (3)

Application Number Priority Date Filing Date Title
US900362 1997-07-25
US09/900,362 US6572576B2 (en) 2001-07-07 2001-07-07 Method and apparatus for leak detection in a fluid line
PCT/US2002/021372 WO2003006944A2 (fr) 2001-07-07 2002-07-08 Procede et appareil permettant de detecter une fuite dans un conduit de fluide

Publications (4)

Publication Number Publication Date
EP1425063A2 EP1425063A2 (fr) 2004-06-09
EP1425063A4 EP1425063A4 (fr) 2009-01-07
EP1425063B1 true EP1425063B1 (fr) 2010-09-08
EP1425063B2 EP1425063B2 (fr) 2018-10-31

Family

ID=25412386

Family Applications (1)

Application Number Title Priority Date Filing Date
EP02761044.3A Expired - Lifetime EP1425063B2 (fr) 2001-07-07 2002-07-08 Systeme permettant de detecter une fuite dans un conduit de fluide

Country Status (7)

Country Link
US (2) US6572576B2 (fr)
EP (1) EP1425063B2 (fr)
JP (1) JP4118233B2 (fr)
AT (1) ATE480275T1 (fr)
AU (1) AU2002326340A1 (fr)
DE (1) DE60237621D1 (fr)
WO (1) WO2003006944A2 (fr)

Families Citing this family (166)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6890315B1 (en) * 2000-05-23 2005-05-10 Chf Solutions, Inc. Method and apparatus for vein fluid removal in heart failure
US6585675B1 (en) * 2000-11-02 2003-07-01 Chf Solutions, Inc. Method and apparatus for blood withdrawal and infusion using a pressure controller
US6689083B1 (en) * 2000-11-27 2004-02-10 Chf Solutions, Inc. Controller for ultrafiltration blood circuit which prevents hypotension by monitoring osmotic pressure in blood
US6773412B2 (en) * 2001-04-13 2004-08-10 Chf Solutions, Inc. User interface for blood treatment device
US6572576B2 (en) * 2001-07-07 2003-06-03 Nxstage Medical, Inc. Method and apparatus for leak detection in a fluid line
US6743193B2 (en) * 2001-07-17 2004-06-01 Nx Stage Medical, Inc. Hermetic flow selector valve
US7241272B2 (en) 2001-11-13 2007-07-10 Baxter International Inc. Method and composition for removing uremic toxins in dialysis processes
US7040142B2 (en) * 2002-01-04 2006-05-09 Nxstage Medical, Inc. Method and apparatus for leak detection in blood circuits combining external fluid detection and air infiltration detection
US20030128125A1 (en) 2002-01-04 2003-07-10 Burbank Jeffrey H. Method and apparatus for machine error detection by combining multiple sensor inputs
US9717840B2 (en) 2002-01-04 2017-08-01 Nxstage Medical, Inc. Method and apparatus for machine error detection by combining multiple sensor inputs
DE10201109C1 (de) * 2002-01-15 2003-01-23 Fresenius Medical Care De Gmbh Verfahren und Vorrichtung zur Detektion einer Leckage in einem Flüssigkeitssystem einer Blutbehandlungsvorrichtung
US6695807B2 (en) 2002-01-18 2004-02-24 Dsu Medical, Inc. Blood flow reversing system
US6796955B2 (en) * 2002-02-14 2004-09-28 Chf Solutions, Inc. Method to control blood and filtrate flowing through an extracorporeal device
US7022098B2 (en) 2002-04-10 2006-04-04 Baxter International Inc. Access disconnection systems and methods
US20040254513A1 (en) 2002-04-10 2004-12-16 Sherwin Shang Conductive polymer materials and applications thereof including monitoring and providing effective therapy
US7052480B2 (en) 2002-04-10 2006-05-30 Baxter International Inc. Access disconnection systems and methods
US10155082B2 (en) 2002-04-10 2018-12-18 Baxter International Inc. Enhanced signal detection for access disconnection systems
US6947131B2 (en) * 2002-05-07 2005-09-20 Chf Solutions, Inc. Blood leak detector for extracorporeal treatment system
EP1531894B1 (fr) * 2002-06-06 2012-08-08 NxStage Medical, Inc. Appareil de traitement de sang comprenant un filtre air/pyrogenes
AU2003249296A1 (en) 2002-07-19 2004-02-09 Baxter Healthcare S.A. Systems and methods for performing peritoneal dialysis
US7901419B2 (en) * 2002-09-04 2011-03-08 Allergan, Inc. Telemetrically controlled band for regulating functioning of a body organ or duct, and methods of making, implantation and use
US7351218B2 (en) * 2002-12-20 2008-04-01 Gambro Lundia Ab Device and process for extracorporeal treatment by citrate anticoagulant
ATE434454T1 (de) 2003-01-07 2009-07-15 Nxstage Medical Inc Chargenfiltriersystem zur herstellung einer sterilen ersatzflüssigkeit für nierenbehandlungen
US20080210606A1 (en) 2004-01-07 2008-09-04 Jeffrey Burbank Filtration System Preparation of Fluids for Medical Applications
US9700663B2 (en) 2005-01-07 2017-07-11 Nxstage Medical, Inc. Filtration system for preparation of fluids for medical applications
US7297270B2 (en) * 2003-04-04 2007-11-20 Chf Solutions, Inc. Hollow fiber filter for extracorporeal blood circuit
US6979306B2 (en) * 2003-08-13 2005-12-27 Moll Family Trust Method and device for monitoring loss of body fluid and dislodgment of medical instrument from body
JP4137751B2 (ja) * 2003-09-19 2008-08-20 日機装株式会社 血液浄化装置
US7671974B2 (en) * 2003-10-29 2010-03-02 Chf Solutions Inc. Cuvette apparatus and system for measuring optical properties of a liquid such as blood
US8038639B2 (en) 2004-11-04 2011-10-18 Baxter International Inc. Medical fluid system with flexible sheeting disposable unit
US8029454B2 (en) 2003-11-05 2011-10-04 Baxter International Inc. High convection home hemodialysis/hemofiltration and sorbent system
WO2005046439A2 (fr) * 2003-11-07 2005-05-26 Nxstage Medical, Inc. Procedes et appareil ameliores permettant de detecter les fuites dans des systemes de traitement sanguin
US7744553B2 (en) 2003-12-16 2010-06-29 Baxter International Inc. Medical fluid therapy flow control systems and methods
US7303540B2 (en) * 2004-04-26 2007-12-04 Chf Solutions, Inc. User interface for blood treatment device
JP4248463B2 (ja) * 2004-08-23 2009-04-02 日機装株式会社 血液浄化装置
JP4094600B2 (ja) * 2004-10-06 2008-06-04 日機装株式会社 血液浄化装置
EP1802363A1 (fr) * 2004-10-22 2007-07-04 Cobe Cardiovascular, Inc. Systemes de perfusion sanguine extracorporel convertible
US7615028B2 (en) * 2004-12-03 2009-11-10 Chf Solutions Inc. Extracorporeal blood treatment and system having reversible blood pumps
US20060130591A1 (en) * 2004-12-21 2006-06-22 Perkins, Corban Enterprises Venous needle dislodgement sensor
US20060161094A1 (en) * 2005-01-14 2006-07-20 Utterberg David S 3D clampable valve flow reversing system
US20070004996A1 (en) * 2005-06-20 2007-01-04 Lovejoy David A Needle disengagement sensing mechanism
US20070010779A1 (en) * 2005-07-07 2007-01-11 Utterberg David S Blood leak monitoring method and apparatus
US20080161723A1 (en) * 2006-09-06 2008-07-03 Optiscan Biomedical Corporation Infusion flow interruption method and apparatus
US20090222671A1 (en) 2005-10-25 2009-09-03 Burbank Jeffrey H Safety features for medical devices requiring assistance and supervision
JP4798653B2 (ja) * 2005-11-18 2011-10-19 日機装株式会社 血液浄化装置
US20070119508A1 (en) * 2005-11-29 2007-05-31 West Richard L Fluid Flow Diversion Valve and Blood Collection System Employing Same
US8043206B2 (en) 2006-01-04 2011-10-25 Allergan, Inc. Self-regulating gastric band with pressure data processing
US7798954B2 (en) 2006-01-04 2010-09-21 Allergan, Inc. Hydraulic gastric band with collapsible reservoir
US8469331B2 (en) * 2006-04-07 2013-06-25 Nxstage Medical, Inc. Filtration system for preparation of fluids for medical applications
US7815588B2 (en) * 2006-06-07 2010-10-19 Paul Sakiewicz Method and device for reversing lines in the procedure of hemodialysis
JP4984685B2 (ja) * 2006-06-30 2012-07-25 澁谷工業株式会社 透析装置の洗浄方法
US7442575B2 (en) * 2006-09-29 2008-10-28 Texas Christian University Method of manufacturing semiconductor nanowires
US20080108955A1 (en) * 2006-11-02 2008-05-08 Blickhan Bryan J Flow Controllers
US20080108954A1 (en) * 2006-11-02 2008-05-08 Jean-Marie Mathias Flow Controllers
US8152751B2 (en) * 2007-02-09 2012-04-10 Baxter International Inc. Acoustic access disconnection systems and methods
US8376978B2 (en) * 2007-02-09 2013-02-19 Baxter International Inc. Optical access disconnection systems and methods
US10463778B2 (en) 2007-02-09 2019-11-05 Baxter International Inc. Blood treatment machine having electrical heartbeat analysis
US9333293B2 (en) * 2007-05-09 2016-05-10 Acist Medical Systems, Inc. Injector device, method, and computer program product for detecting a vacuum within a syringe
CN101678165B (zh) * 2007-06-13 2012-05-23 川澄化学工业株式会社 血液净化装置及其回路连接不良的确认方法
US8057423B2 (en) 2007-07-05 2011-11-15 Baxter International Inc. Dialysis system having disposable cassette
DE102007039581A1 (de) * 2007-08-22 2009-02-26 Fresenius Medical Care Deutschland Gmbh Vorrichtung und Verfahren zur Überwachung eines Zugangs zu einem Patienten
US8597505B2 (en) 2007-09-13 2013-12-03 Fresenius Medical Care Holdings, Inc. Portable dialysis machine
US9358331B2 (en) 2007-09-13 2016-06-07 Fresenius Medical Care Holdings, Inc. Portable dialysis machine with improved reservoir heating system
US9308307B2 (en) 2007-09-13 2016-04-12 Fresenius Medical Care Holdings, Inc. Manifold diaphragms
US8535522B2 (en) 2009-02-12 2013-09-17 Fresenius Medical Care Holdings, Inc. System and method for detection of disconnection in an extracorporeal blood circuit
US20090076434A1 (en) * 2007-09-13 2009-03-19 Mischelevich David J Method and System for Achieving Volumetric Accuracy in Hemodialysis Systems
US8105487B2 (en) 2007-09-25 2012-01-31 Fresenius Medical Care Holdings, Inc. Manifolds for use in conducting dialysis
US9199022B2 (en) 2008-09-12 2015-12-01 Fresenius Medical Care Holdings, Inc. Modular reservoir assembly for a hemodialysis and hemofiltration system
US8475399B2 (en) 2009-02-26 2013-07-02 Fresenius Medical Care Holdings, Inc. Methods and systems for measuring and verifying additives for use in a dialysis machine
US8240636B2 (en) 2009-01-12 2012-08-14 Fresenius Medical Care Holdings, Inc. Valve system
US8040493B2 (en) 2007-10-11 2011-10-18 Fresenius Medical Care Holdings, Inc. Thermal flow meter
US20090101577A1 (en) * 2007-09-28 2009-04-23 Fulkerson Barry N Methods and Systems for Controlling Ultrafiltration Using Central Venous Pressure Measurements
US8221320B2 (en) * 2007-09-21 2012-07-17 Baxter International Inc. Access disconnect detection system
US8197431B2 (en) 2007-09-21 2012-06-12 Baxter International Inc. Acoustic access disconnect detection system
US8444587B2 (en) 2007-10-01 2013-05-21 Baxter International Inc. Fluid and air handling in blood and dialysis circuits
US8033157B2 (en) 2007-10-01 2011-10-11 Baxter International Inc. Medical fluid air bubble detection apparatus and method
EP2192937B1 (fr) * 2007-10-04 2011-12-07 Gambro Lundia AB Appareil de perfusion
US8123947B2 (en) * 2007-10-22 2012-02-28 Baxter International Inc. Priming and air removal systems and methods for dialysis
US8114276B2 (en) 2007-10-24 2012-02-14 Baxter International Inc. Personal hemodialysis system
US9415150B2 (en) 2007-11-09 2016-08-16 Baxter Healthcare S.A. Balanced flow dialysis machine
CA3057806C (fr) 2007-11-29 2021-11-23 Fresenius Medical Care Holdings, Inc. Systeme et procede pour realiser une hemodialyse et une hemofiltration
US9026370B2 (en) 2007-12-18 2015-05-05 Hospira, Inc. User interface improvements for medical devices
US20090218535A1 (en) * 2008-02-27 2009-09-03 Andres Pasko Flow controllers for fluid circuits
CA2717886C (fr) 2008-04-01 2015-02-10 Gambro Lundia Ab Appareil et procede pour surveiller un acces vasculaire
US8652082B2 (en) * 2008-04-15 2014-02-18 Gambro Lundia Ab Blood treatment apparatus
CA2721288C (fr) * 2008-04-15 2017-01-03 Gambro Lundia Ab Procede et appareil de traitement du sang
JP5529123B2 (ja) 2008-06-26 2014-06-25 ガンブロ・ルンディア・エービー 方法、および流体接続の完全性をモニターするための装置
US8192388B2 (en) * 2008-07-25 2012-06-05 Baxter International Inc. System and method for detecting access disconnection
US8114043B2 (en) 2008-07-25 2012-02-14 Baxter International Inc. Electromagnetic induction access disconnect sensor
US20100184198A1 (en) * 2009-01-16 2010-07-22 Joseph Russell T Systems and Methods of Urea Processing to Reduce Sorbent Load
AU2009302327C1 (en) 2008-10-07 2015-09-10 Fresenius Medical Care Holdings, Inc. Priming system and method for dialysis systems
US20100100026A1 (en) * 2008-10-16 2010-04-22 Fresenius Medical Care Holdings, Inc. Wetness sensor utilizing passive resonant circuits
WO2010044801A1 (fr) * 2008-10-17 2010-04-22 Emory University Systèmes et procédés pour éviter une erreur de transfusion
US20100185049A1 (en) 2008-10-22 2010-07-22 Allergan, Inc. Dome and screw valves for remotely adjustable gastric banding systems
KR101508483B1 (ko) 2008-10-30 2015-04-06 프레제니우스 메디칼 케어 홀딩스 인코퍼레이티드 모듈화된 휴대용 투석장치
US9370324B2 (en) 2008-11-05 2016-06-21 Fresenius Medical Care Holdings, Inc. Hemodialysis patient data acquisition, management and analysis system
EP3178387A1 (fr) 2009-06-26 2017-06-14 Gambro Lundia AB Dispositifs, produit-programme informatique et procédé d'extraction de données
US8753515B2 (en) 2009-12-05 2014-06-17 Home Dialysis Plus, Ltd. Dialysis system with ultrafiltration control
CA2785767A1 (fr) 2009-12-28 2011-07-07 Gambro Lundia Ab Appareil et procede de prediction d'une chute symptomatique rapide de la pression arterielle
US8840541B2 (en) 2010-02-25 2014-09-23 Apollo Endosurgery, Inc. Pressure sensing gastric banding system
US8939888B2 (en) 2010-04-28 2015-01-27 Apollo Endosurgery, Inc. Method and system for determining the pressure of a fluid in a syringe, an access port, a catheter, and a gastric band
US20110270025A1 (en) 2010-04-30 2011-11-03 Allergan, Inc. Remotely powered remotely adjustable gastric band system
US8501009B2 (en) 2010-06-07 2013-08-06 State Of Oregon Acting By And Through The State Board Of Higher Education On Behalf Of Oregon State University Fluid purification system
JPWO2012017959A1 (ja) * 2010-08-05 2013-10-03 日機装株式会社 血液浄化装置及びその液漏れ検査方法
US9194792B2 (en) 2010-09-07 2015-11-24 Fresenius Medical Care Holdings, Inc. Blood chamber for an optical blood monitoring system
US8517968B2 (en) 2011-02-25 2013-08-27 Fresenius Medical Care Holdings, Inc. Shrouded sensor clip assembly and blood chamber for an optical blood monitoring system
US8743354B2 (en) 2010-09-07 2014-06-03 Fresenius Medical Care Holdings, Inc. Shrouded sensor clip assembly and blood chamber for an optical blood monitoring system
GB201019228D0 (en) * 2010-11-15 2010-12-29 Corp Dialysis device and method of dialysis
CN103347550A (zh) 2010-11-17 2013-10-09 弗雷泽纽斯医疗保健控股公司 用于光学监视系统的传感器夹组件
US9173988B2 (en) 2010-11-17 2015-11-03 Fresenius Medical Care Holdings, Inc. Sensor clip assembly for an optical monitoring system
US8725435B2 (en) 2011-04-13 2014-05-13 Apollo Endosurgery, Inc. Syringe-based leak detection system
US9724459B2 (en) 2011-08-15 2017-08-08 Nxstage Medical, Inc. Medical device leak sensing devices, methods, and systems
WO2013028524A1 (fr) 2011-08-19 2013-02-28 Hospira, Inc. Système de reconnaissance de modèle, et procédé de détection de gouttelettes de fluide coincées dans une conduite d'administration de fluide d'un système de perfusion
WO2013028497A1 (fr) 2011-08-19 2013-02-28 Hospira, Inc. Systèmes et procédés pour une interface graphique comprenant une représentation graphique de données médicales
AU2012318561B2 (en) 2011-10-07 2017-04-20 Outset Medical, Inc. Heat exchange fluid purification for dialysis system
US20130146541A1 (en) 2011-12-13 2013-06-13 Nxstage Medical, Inc. Fluid purification methods, devices, and systems
US10022498B2 (en) 2011-12-16 2018-07-17 Icu Medical, Inc. System for monitoring and delivering medication to a patient and method of using the same to minimize the risks associated with automated therapy
USD725261S1 (en) 2012-02-24 2015-03-24 Fresenius Medical Care Holdings, Inc. Blood flow chamber
EP2825815A4 (fr) 2012-03-16 2015-12-23 1589549 Alberta Ltd Procédé de réduction des fuites d'un pipeline
US10328193B2 (en) * 2012-03-21 2019-06-25 Gambro Lundia Ab Extracorporeal blood treatment apparatus with multiple treatment solution reservoirs
US9995611B2 (en) 2012-03-30 2018-06-12 Icu Medical, Inc. Air detection system and method for detecting air in a pump of an infusion system
ES2743160T3 (es) 2012-07-31 2020-02-18 Icu Medical Inc Sistema de cuidado de pacientes para medicaciones críticas
US9415151B2 (en) * 2012-09-25 2016-08-16 Fresenius Medical Care Holdings, Inc. Blood flow reversal valves and related systems and methods
EP2737918B1 (fr) * 2012-11-29 2016-06-01 Gambro Lundia AB Détection de fuite de port en ligne d'hémodialyse
DE102012024341B3 (de) * 2012-12-13 2014-02-13 Fresenius Medical Care Deutschland Gmbh Vorrichtung und Verfahren zum Überwachen eines extrakorporalen Blutkreislaufs zur Erkennung von Luftblasen
US9201036B2 (en) 2012-12-21 2015-12-01 Fresenius Medical Care Holdings, Inc. Method and system of monitoring electrolyte levels and composition using capacitance or induction
US9157786B2 (en) 2012-12-24 2015-10-13 Fresenius Medical Care Holdings, Inc. Load suspension and weighing system for a dialysis machine reservoir
US10065003B2 (en) 2012-12-28 2018-09-04 Gambro Lundia Ab Syringe pump engagement detection apparatus and methods
CN104394900A (zh) * 2012-12-31 2015-03-04 甘布罗伦迪亚肾脏产品公司 体外血液处理装置中基于压力的泄漏检测
US9623164B2 (en) * 2013-02-01 2017-04-18 Medtronic, Inc. Systems and methods for multifunctional volumetric fluid control
US20140263062A1 (en) 2013-03-14 2014-09-18 Fresenius Medical Care Holdings, Inc. Universal portable machine for online hemodiafiltration using regenerated dialysate
US9433720B2 (en) 2013-03-14 2016-09-06 Fresenius Medical Care Holdings, Inc. Universal portable artificial kidney for hemodialysis and peritoneal dialysis
AU2014234479B2 (en) 2013-03-20 2018-08-02 Gambro Lundia Ab Monitoring of cardiac arrest in a patient connected to an extracorporeal blood processing apparatus
WO2014190264A1 (fr) 2013-05-24 2014-11-27 Hospira, Inc. Système de perfusion à multiples capteurs pour détecter la présence d'air ou d'une occlusion dans le système de perfusion
WO2014194089A1 (fr) 2013-05-29 2014-12-04 Hospira, Inc. Système de perfusion qui emploie un ou plusieurs capteurs et des informations additionnelles pour faire une détermination d'air concernant le système de perfusion
EP3003442B1 (fr) 2013-05-29 2020-12-30 ICU Medical, Inc. Système de perfusion et procédé d'utilisation évitant la sursaturation d'un convertisseur analogique-numérique
DE102013012366B3 (de) 2013-07-25 2014-12-31 Fresenius Medical Care Deutschland Gmbh Extrakorporale Blutbehandlungsvorrichtung
DE102013016469A1 (de) * 2013-10-04 2015-04-09 Fresenius Medical Care Deutschland Gmbh Blutbehandlungsvorrichtung und Verfahren zur Überwachung des Zustandes eines Abschnitts eines extrakorporalen Blutkreislaufs
US9354640B2 (en) * 2013-11-11 2016-05-31 Fresenius Medical Care Holdings, Inc. Smart actuator for valve
WO2015095239A1 (fr) 2013-12-18 2015-06-25 Optiscan Biomedical Corporation Systèmes et procédés de détection de fuites
EP3110474B1 (fr) 2014-02-28 2019-12-18 ICU Medical, Inc. Système de perfusion et procédé qui utilise la détection optique de bulles d'air à double longueur d'onde
DE102014102731A1 (de) * 2014-02-28 2015-09-03 B. Braun Avitum Ag Vorrichtung und Verfahren zur Erkennung einer venösen Nadeldiskonnektion
EP3838308A1 (fr) 2014-04-29 2021-06-23 Outset Medical, Inc. Système et procédés de dialyse
US11344673B2 (en) 2014-05-29 2022-05-31 Icu Medical, Inc. Infusion system and pump with configurable closed loop delivery rate catch-up
US10980929B2 (en) 2014-09-12 2021-04-20 Diality Inc. Hemodialysis system with ultrafiltration controller
US10172989B2 (en) 2014-09-12 2019-01-08 Easydial Inc. Portable hemodialysis machine and disposable cartridge with blood leak sensor
US9498567B2 (en) * 2014-09-29 2016-11-22 Fenwal, Inc. Systems and methods for controlling the return phase of a blood separation procedure
US9486590B2 (en) 2014-09-29 2016-11-08 Fenwal, Inc. Automatic purging of air from a fluid processing system
US11344668B2 (en) 2014-12-19 2022-05-31 Icu Medical, Inc. Infusion system with concurrent TPN/insulin infusion
US10850024B2 (en) 2015-03-02 2020-12-01 Icu Medical, Inc. Infusion system, device, and method having advanced infusion features
USD799031S1 (en) 2015-09-09 2017-10-03 Fresenius Medical Care Holdings, Inc. Blood flow chamber with directional arrow
US10413654B2 (en) 2015-12-22 2019-09-17 Baxter International Inc. Access disconnection system and method using signal metrics
ES2912378T3 (es) 2016-05-13 2022-05-25 Icu Medical Inc Sistema de bomba de infusión con purga automática de línea común
JP6762772B2 (ja) * 2016-06-08 2020-09-30 日機装株式会社 血液浄化装置及びその接続確認方法
EP3468635A4 (fr) 2016-06-10 2019-11-20 ICU Medical, Inc. Capteur de flux acoustique pour mesures continues de débit de médicament et commande par rétroaction de perfusion
JP7025408B2 (ja) 2016-08-19 2022-02-24 アウトセット・メディカル・インコーポレイテッド 腹膜透析システム及び方法
US11826545B2 (en) 2016-09-08 2023-11-28 Fresenius Medical Care Holdings, Inc. Optical blood detection system
US10838152B2 (en) 2017-11-17 2020-11-17 Senko Advanced Components, Inc. Ultra-small form factor optical connector having dual alignment keys
US20200271232A1 (en) * 2017-10-06 2020-08-27 Nipro Corporation Flow path switching device
US10089055B1 (en) 2017-12-27 2018-10-02 Icu Medical, Inc. Synchronized display of screen content on networked devices
US11278671B2 (en) 2019-12-04 2022-03-22 Icu Medical, Inc. Infusion pump with safety sequence keypad
EP3834861B1 (fr) * 2019-12-13 2024-03-06 Gambro Lundia AB Module complémentaire de traitement extracorporel du sang et circuit pour le sang fourni avec ledit module complémentaire
JP7463764B2 (ja) 2020-02-27 2024-04-09 ニプロ株式会社 漏液抑制装置および導入液回路閉塞装置
EP4185260A1 (fr) 2020-07-21 2023-05-31 ICU Medical, Inc. Dispositifs de transfert de fluide et procédés d'utilisation
US11135360B1 (en) 2020-12-07 2021-10-05 Icu Medical, Inc. Concurrent infusion with common line auto flush
CN114993581B (zh) * 2022-08-02 2022-10-25 深圳赛桥生物创新技术有限公司 一种管路气密性检测装置、方法及系统

Family Cites Families (46)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3648694A (en) * 1968-09-25 1972-03-14 Inst Oncologic Bucharest Automatic system with perfusion protection against malfunction
NL158390B (nl) 1973-11-26 1978-11-15 Rhone Poulenc Sa Inrichting voor buitenlichamelijke bloedkringloop voor dialyse.
US3935876A (en) * 1974-11-15 1976-02-03 Renal Systems, Inc. Air leak detector
JPS5911864B2 (ja) 1975-07-14 1984-03-19 武田薬品工業株式会社 漏血検知装置
DE2613281C2 (de) 1976-03-29 1984-12-20 Günter van Dr.med. 4000 Düsseldorf Endert Doppellumenkatheter
DE2703087C2 (de) 1977-01-26 1984-11-29 Günter van Dr.med. 4000 Düsseldorf Endert Doppellumenkatheter
JPS5814223B2 (ja) 1979-02-24 1983-03-17 株式会社メデクス 透析「ろ」過装置
US4324662A (en) 1979-12-28 1982-04-13 Baxter Travenol Laboratories, Inc. Flow reversal in a dialyzer
US4364261A (en) 1981-03-25 1982-12-21 N.E.R.G. Enterprises, Inc. Multi-media leak test apparatus
DE3209845A1 (de) * 1982-03-18 1983-09-29 Küppersbusch AG, 4650 Gelsenkirchen Fluessigkeitsfoerdereinrichtung mit einem sensor
US4490135A (en) † 1982-09-24 1984-12-25 Extracorporeal Medical Specialties, Inc. Single needle alternating blood flow system
FR2548541B1 (fr) 1983-07-07 1986-09-12 Rhone Poulenc Sa Procede de plasmapherese et appareillage utilisable notamment pour ce procede
US4828543A (en) † 1986-04-03 1989-05-09 Weiss Paul I Extracorporeal circulation apparatus
BE905615R (nl) 1986-09-10 1987-04-17 Hombrouckx Remi O J Methode en apparatuur voor eennaaldhemodialyse.
US4885087A (en) 1986-11-26 1989-12-05 Kopf Henry B Apparatus for mass transfer involving biological/pharmaceutical media
FR2660866B1 (fr) 1990-04-13 1992-06-12 Hogamed Procede et dispositif de preparation d'un liquide de substitution.
US5336165A (en) * 1991-08-21 1994-08-09 Twardowski Zbylut J Artificial kidney for frequent (daily) Hemodialysis
JPH06261938A (ja) † 1992-07-07 1994-09-20 Senko Ika Kogyo Kk 透析装置及び返血方法
US5468390A (en) 1992-11-23 1995-11-21 Rensselaer Polytechnic Institute Low fouling ultrafiltration and microfiltration aryl polysulfone
US5368555A (en) 1992-12-29 1994-11-29 Hepatix, Inc. Organ support system
GB2276566A (en) 1993-03-24 1994-10-05 Saitekku Kabushiki Kaisha Haemodialyser unit
US5624551A (en) 1993-04-28 1997-04-29 Fresenius Ag Hydraulic safety circuit for a hemodialysis apparatus
US5394732A (en) 1993-09-10 1995-03-07 Cobe Laboratories, Inc. Method and apparatus for ultrasonic detection of air bubbles
FR2710538B1 (fr) 1993-09-30 1995-12-01 Becton Dickinson Co Procédé et dispositif de détection de bulles dans une ligne de perfusion.
US5643190A (en) 1995-01-17 1997-07-01 Medisystems Technology Corporation Flow-through treatment device
US5591344A (en) * 1995-02-13 1997-01-07 Aksys, Ltd. Hot water disinfection of dialysis machines, including the extracorporeal circuit thereof
DE19528907C1 (de) † 1995-08-05 1996-11-07 Fresenius Ag Vorrichtung zur Ermittlung hämodynamischer Parameter während einer extrakorporalen Blutbehandlung
SE508374C2 (sv) 1995-09-12 1998-09-28 Gambro Med Tech Ab Förfarande och anordning för detektering av tillståndet hos en blodkärlsaccess
FR2749190B1 (fr) 1996-05-28 1998-09-18 Omnium Traitement Valorisa Procede et installation pour tester in situ l'integrite des membranes de filtration
DE19700466A1 (de) 1997-01-09 1998-07-16 Polaschegg Hans Dietrich Dr Einrichtung und Verfahren zur Hämodiafiltration
SE512266C2 (sv) 1997-07-09 2000-02-21 Gambro Med Tech Ab Förfarande och anordning för integritetstest av ett slangset avsett för användning i en cykler för peritonealdialys
US6269679B1 (en) 1997-10-17 2001-08-07 The Regents Of The University Of California System and method to characterize gas transport properties
US6189388B1 (en) 1997-11-12 2001-02-20 Gambro, Inc. Access flow monitoring using reversal of normal blood flow
EP1061961B1 (fr) 1998-01-23 2004-12-01 ViaCirQ, Inc. Appareils et procedes destines au traitement par hyperthermie generalisee
US6177049B1 (en) 1998-06-10 2001-01-23 Dsu Medical Corporation Reversing flow blood processing system
US5894011A (en) 1998-06-24 1999-04-13 Prosl; Frank R. Flow reversing device for hemodialysis
SE513838C2 (sv) * 1998-06-25 2000-11-13 Gambro Lundia Ab Metod jämte anordning för kalibrering av avkännande medel i ett system med ett strömmande fluidum
DE19832451C1 (de) 1998-07-18 1999-08-26 Fresenius Medical Care De Gmbh Verfahren und Vorrichtung zum Überprüfen des ordnungsgemäßen Austauschs eines gebrauchten Filters in einer Vorrichtung zur extrakorporalen Blutbehandlung
US6044691A (en) 1998-08-26 2000-04-04 Aksys, Ltd. Blood tubing set integrity tests for extracorporeal circuits
DE19848235C1 (de) 1998-10-20 2000-03-16 Fresenius Medical Care De Gmbh Verfahren zur Überwachung eines Gefäßzuganges und Vorrichtung zur extrakorporalen Blutbehandlung mit einer Einrichtung zur Überwachung des Gefäßzuganges
US6319465B1 (en) † 1999-06-03 2001-11-20 Dsu Medical Corporation Reversing flow blood processing system having reduced clotting potential
US6401518B1 (en) 1999-07-29 2002-06-11 General Electric Company Fluid filled electrical device with diagnostic sensor located in fluid circulation flow path
US6284142B1 (en) * 1999-09-03 2001-09-04 Baxter International Inc. Sensing systems and methods for differentiating between different cellular blood species during extracorporeal blood separation or processing
WO2002026288A2 (fr) 2000-09-27 2002-04-04 Cobe Cardiovascular, Inc. Cartouche jetable pour systeme de perfusion sanguine
US6585675B1 (en) * 2000-11-02 2003-07-01 Chf Solutions, Inc. Method and apparatus for blood withdrawal and infusion using a pressure controller
US6572576B2 (en) * 2001-07-07 2003-06-03 Nxstage Medical, Inc. Method and apparatus for leak detection in a fluid line

Also Published As

Publication number Publication date
EP1425063A2 (fr) 2004-06-09
US6572576B2 (en) 2003-06-03
JP4118233B2 (ja) 2008-07-16
AU2002326340A1 (en) 2003-01-29
US20040243046A1 (en) 2004-12-02
US7087033B2 (en) 2006-08-08
EP1425063B2 (fr) 2018-10-31
ATE480275T1 (de) 2010-09-15
EP1425063A4 (fr) 2009-01-07
US20030009123A1 (en) 2003-01-09
DE60237621D1 (de) 2010-10-21
WO2003006944A2 (fr) 2003-01-23
JP2005525129A (ja) 2005-08-25
WO2003006944A3 (fr) 2003-10-09

Similar Documents

Publication Publication Date Title
EP1425063B1 (fr) Systeme permettant de detecter une fuite dans un conduit de fluide
EP1691882B1 (fr) Appareils ameliorés permettant de detecter les fuites dans des systemes de traitement sanguin
US7040142B2 (en) Method and apparatus for leak detection in blood circuits combining external fluid detection and air infiltration detection
AU730338B2 (en) Method and device for monitoring vessel access during extracorporeal blood treatment
US6077443A (en) Method and device for monitoring a vascular access during a dialysis treatment
US7004924B1 (en) Methods, systems, and kits for the extracorporeal processing of blood
US8180443B1 (en) Device and method for monitoring a patient access, in particular a vascular access in extracorporeal blood treatment
US20100234787A1 (en) Hemodialysis apparatus
JP2009500108A (ja) 血液漏洩監視方法及び装置
KR20110042189A (ko) 접속 분리를 검출하기 위한 시스템 및 방법
US20040186415A1 (en) Blood circuit with leak-safe features
CA2913091A1 (fr) Procede et dispositif de surveillance d'un circuit sanguin extracorporel
EP3415180B1 (fr) Système à sécurité intégrée et procédé pour une procédure de fluide médical
US11324868B2 (en) Device for extracorporeal blood treatment and device for collecting blood clots, and method for determining a hemodynamic parameter during an extracorporeal blood treatment
JPH0675504U (ja) 回路クランプ駆動制御装置
JP2005065888A (ja) 血管アクセス監視方法および医療装置
EP3636296A1 (fr) Appareil de traitement sanguin extracorporel et procédé de surveillance de pressions dans un appareil de traitement sanguin extracorporel
CN108136101A (zh) 用于以基于压力的方式识别血块的设备、系统和方法

Legal Events

Date Code Title Description
PUAI Public reference made under article 153(3) epc to a published international application that has entered the european phase

Free format text: ORIGINAL CODE: 0009012

17P Request for examination filed

Effective date: 20040204

AK Designated contracting states

Kind code of ref document: A2

Designated state(s): AT BE BG CH CY CZ DE DK EE ES FI FR GB GR IE IT LI LU MC NL PT SE SK TR

AX Request for extension of the european patent

Extension state: AL LT LV MK RO SI

A4 Supplementary search report drawn up and despatched

Effective date: 20081204

RIC1 Information provided on ipc code assigned before grant

Ipc: A61M 1/36 20060101AFI20081128BHEP

17Q First examination report despatched

Effective date: 20090219

RTI1 Title (correction)

Free format text: SYSTEM FOR LEAK DETECTION IN A FLUID LINE

GRAP Despatch of communication of intention to grant a patent

Free format text: ORIGINAL CODE: EPIDOSNIGR1

GRAS Grant fee paid

Free format text: ORIGINAL CODE: EPIDOSNIGR3

GRAA (expected) grant

Free format text: ORIGINAL CODE: 0009210

AK Designated contracting states

Kind code of ref document: B1

Designated state(s): AT BE BG CH CY CZ DE DK EE ES FI FR GB GR IE IT LI LU MC NL PT SE SK TR

REG Reference to a national code

Ref country code: GB

Ref legal event code: FG4D

REG Reference to a national code

Ref country code: CH

Ref legal event code: EP

REG Reference to a national code

Ref country code: IE

Ref legal event code: FG4D

REF Corresponds to:

Ref document number: 60237621

Country of ref document: DE

Date of ref document: 20101021

Kind code of ref document: P

REG Reference to a national code

Ref country code: NL

Ref legal event code: VDEP

Effective date: 20100908

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: AT

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20100908

Ref country code: FI

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20100908

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: CY

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20100908

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: SE

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20100908

Ref country code: NL

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20100908

Ref country code: GR

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20101209

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: PT

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20110110

Ref country code: EE

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20100908

Ref country code: SK

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20100908

Ref country code: CZ

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20100908

PLBI Opposition filed

Free format text: ORIGINAL CODE: 0009260

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: BE

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20100908

Ref country code: ES

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20101219

PLAX Notice of opposition and request to file observation + time limit sent

Free format text: ORIGINAL CODE: EPIDOSNOBS2

26 Opposition filed

Opponent name: FRESENIUS MEDICAL CARE DEUTSCHLAND GMBH

Effective date: 20110608

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: DK

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20100908

REG Reference to a national code

Ref country code: DE

Ref legal event code: R026

Ref document number: 60237621

Country of ref document: DE

Effective date: 20110608

PLAF Information modified related to communication of a notice of opposition and request to file observations + time limit

Free format text: ORIGINAL CODE: EPIDOSCOBS2

PLBB Reply of patent proprietor to notice(s) of opposition received

Free format text: ORIGINAL CODE: EPIDOSNOBS3

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: MC

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20110731

REG Reference to a national code

Ref country code: CH

Ref legal event code: PL

REG Reference to a national code

Ref country code: IE

Ref legal event code: MM4A

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: LI

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20110731

Ref country code: CH

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20110731

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: IE

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20110708

APBM Appeal reference recorded

Free format text: ORIGINAL CODE: EPIDOSNREFNO

APBP Date of receipt of notice of appeal recorded

Free format text: ORIGINAL CODE: EPIDOSNNOA2O

APAH Appeal reference modified

Free format text: ORIGINAL CODE: EPIDOSCREFNO

APBQ Date of receipt of statement of grounds of appeal recorded

Free format text: ORIGINAL CODE: EPIDOSNNOA3O

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: LU

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20110708

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: TR

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20100908

Ref country code: BG

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20101208

REG Reference to a national code

Ref country code: FR

Ref legal event code: PLFP

Year of fee payment: 15

REG Reference to a national code

Ref country code: FR

Ref legal event code: PLFP

Year of fee payment: 16

APBU Appeal procedure closed

Free format text: ORIGINAL CODE: EPIDOSNNOA9O

REG Reference to a national code

Ref country code: FR

Ref legal event code: PLFP

Year of fee payment: 17

PUAH Patent maintained in amended form

Free format text: ORIGINAL CODE: 0009272

STAA Information on the status of an ep patent application or granted ep patent

Free format text: STATUS: PATENT MAINTAINED AS AMENDED

27A Patent maintained in amended form

Effective date: 20181031

AK Designated contracting states

Kind code of ref document: B2

Designated state(s): AT BE BG CH CY CZ DE DK EE ES FI FR GB GR IE IT LI LU MC NL PT SE SK TR

REG Reference to a national code

Ref country code: DE

Ref legal event code: R102

Ref document number: 60237621

Country of ref document: DE

PGFP Annual fee paid to national office [announced via postgrant information from national office to epo]

Ref country code: IT

Payment date: 20210721

Year of fee payment: 20

Ref country code: FR

Payment date: 20210726

Year of fee payment: 20

PGFP Annual fee paid to national office [announced via postgrant information from national office to epo]

Ref country code: GB

Payment date: 20210727

Year of fee payment: 20

Ref country code: DE

Payment date: 20210728

Year of fee payment: 20

REG Reference to a national code

Ref country code: DE

Ref legal event code: R071

Ref document number: 60237621

Country of ref document: DE

REG Reference to a national code

Ref country code: GB

Ref legal event code: PE20

Expiry date: 20220707

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: GB

Free format text: LAPSE BECAUSE OF EXPIRATION OF PROTECTION

Effective date: 20220707